Method for measuring the plasma concentration of an analyte directly on a whole blood sample

ABSTRACT

A method of measuring an analyte amount in a whole blood sample, including:
         measuring the haematocrit level of the whole blood sample;   measuring an analyte amount directly in the whole blood sample; and   calculating a corrected analyte amount according to relation:
 
 D   P   =P   a ( D   ST   , D   H )
 
where D P  is the corrected analyte amount, D ST  is the measured analyte amount, D H  is the measured haematocrit level, and P a  is a non-constant polynomial of a degree greater than or equal to 1 having as indeterminate values the measured analyte amount, D ST , and the measured haematocrit level, D H , and having its polynomial coefficients depending on the analyte.

FIELD OF THE INVENTION

The present invention relates to the analysis of biological samples, andmore particularly to the measurement of the concentration or of theamount of an analyte in a blood sample. The invention particularly findsan application in immunoassay measurements of ELISA, ELFA, orimmunocapture type.

BACKGROUND OF THE INVENTION

Usually, the search for an analyte of interest and for the concentrationthereof in a whole blood sample likely to contain said analyte ofinterest comprises, first, separating the plasma from the red cells,particularly by centrifugation, and then measuring the analyteconcentration in the plasma.

The “whole blood” corresponds to a biological sample comprising bloodwith all its components and thus, in particular, the plasma and the redcells. It may for example be blood sampled from a man or an animalwithout any transformation, or the same blood to which adjuvants havebeen added, for example, anticoagulants.

Among concentration measurement methods, techniques are known whichcomprise modifying a measurable property, for example, an optical,electrical, chemical, pH, or enzyme property, according to the quantityof analytes in a blood sample, especially so-called direct, indirect,and competitive ELISA (“Enzyme-Linked ImmunoSorbent Assay”), ELFA(“Enzyme-Linked Fluorescence Assay”), and immunocapture techniques.

FIG. 1 schematically illustrates the main steps of a direct ELISAmeasurement, also called “sandwich” ELISA since it involves two partnersfor binding to the analyte, where, for example, the analyte is anantigen and the two binding partners are antibodies each comprising asite, or epitope, different from each other and each capable of bindingto said antigen provided with a complementary site. The ELISAmeasurement comprises, in its simplest version:

-   -   coating the surface of a solid support, such as a well, for        example, with a layer of a first binding partner of the analyte        which is desired to be detected or the concentration of which is        desired to be measured, where the first binding partner exhibits        a site complementary to the analyte (FIG. 1A);    -   pouring the blood sample, such as plasma originating from the        centrifugation of a whole blood sample, into the well (FIG. 1B)        so that the analytes present in the plasma conjugate with the        first binding partners fixed to the well wall (FIG. 1C);    -   performing a first washing of the well to remove the elements of        no interest for the ongoing analysis, for example, antibodies        and antigens which are not searched for (FIG. 1D);    -   pouring into the well second binding partners for the analyte,        each provided (i) with a site, complementary to one of the free        sites of the analytes immobilized by means of the first binding        partners and different from the complementary site of the first        binding partner, and (ii) with a component having an enzyme        function capable of catalyzing a hydrolysis of a substrate which        changes color according to the quantity of catalyzed hydrogen        (FIG. 1E). Such second binding partners containing an enzyme        function are called “conjugates”;    -   performing a second washing of the well to remove excess        conjugates (FIG. 1F);    -   adding substrate degradable by the enzyme function of the        conjugates into the well and measuring the chrominance or        optical density of the medium contained in the well by        spectrometry (FIG. 1G).

Since chrominance directly depends on the quantity or amount of analytesimmobilized by the first binding partners fixed to the wall of the solidsupport, the measurement of this optical property thus is an indirectmeasurement of the total quantity of analytes present in the plasmasample, and accordingly, knowing the volume of the sample, of theanalyte concentration therein. The measured chrominance is thentransformed, by means of a predetermined mathematical model, into anamount and/or concentration value. “Amount” thus means a quantity ofanalytes in a sample. “Concentration” means an amount divided by thevolume of the sample whereon the measurement is performed.

“Competitive” ELISA involves a single binding partner for the analyte,which exhibits a site complementary to one of the sites of the analyte,as well as a compound which competes with the analyte to be assayed.Once of these two elements then has an enzyme function capable ofcatalyzing a hydrolysis of a substrate which changes color according tothe quantity of catalyzed hydrolysis. The amount and thus theconcentration are thus inversely proportional to the read chrominance.

ELFA measurements are similar to ELISA measurements, but for the factthat the substrate catalyzed by the enzyme function generatesfluorescence measured, for example, by a fluorometer.

All these measurement techniques provide elements only fixing theanalytes having their concentration desired to be measured. Althoughonly the latter are specifically fixed, it can however be observed thatthe nature of the sample substantially influences the amountmeasurement, especially when the reaction time is decreased due todiagnosis-related time constraints. Thus, when the measurement isdirectly performed on a whole blood sample, the measured amount issmaller than that which is directly measured on a plasma sample,particularly due to the presence of haematocrit, which has a matrixeffect.

As known per se, the haematocrit level, or haematocrit, corresponds tothe relative volume occupied by red cells relative to the whole bloodvolume. Certain manufacturers of immunoassay instrument using, as asample for the diagnosis, a whole blood sample instead of a plasmasample, have provided correcting the analyte amount measured in a wholeblood sample according to the following formula:

$\begin{matrix}{D_{p} = \frac{D_{ST}}{1 - \frac{D_{H}}{100}}} & (1)\end{matrix}$where D_(p) is the corrected analyte amount, D_(ST) is the analyteamount directly measured on a whole blood sample, D_(H) is a measurementof the haematocrit level of the whole blood sample. It should be notedthat relation (1) may also apply with the measured and corrected analyteconcentrations instead of the corresponding amounts. However, such acorrection, which is similar to a simple rule of three, does not providegood results.

To date, the amount of an analyte, and accordingly the concentrationthereof, is thus mainly determined on plasma, this measurement being theonly one considered as reliable and reproducible. Further, such ameasurement has the advantage of being independent from the haematocritlevel, which is variable from one subject to the other.

Now, the obtaining of plasma requires a prior centrifugation step, andthus time and specific equipment. Not only may time be a crucialparameter in the case of medical diagnosis, especially when there athreats on the subject's life, but this further assumes a large quantityof centrifuges in a laboratory in charge of a large number of analyses.

SUMMARY OF THE INVENTION

The present invention aims at providing a method of measuring theamount, and thus the concentration, of an analyte directly on a wholeblood sample with a sufficient level of accuracy, thus enabling, inparticular, to avoid the prior centrifugation step, while providing ameasurement independent from the haematocrit level.

For this purpose, the invention aims at a method of measuring an amountof analyte in a whole blood sample, which comprises:

-   -   measuring the haematocrit level of the whole blood sample;    -   measuring an analyte amount directly in the whole blood sample;        and    -   calculating a corrected analyte amount according to relation:        D _(P) =P _(a)(D _(ST) , D _(H))        where D_(p) is the corrected analyte amount, D_(ST) is the        measured analyte amount, D_(H) is the measured haematocrit        level, and P_(a) is a non-constant polynomial of a degree        greater than or equal to 1 having as indeterminate values the        measured analyte amount, D_(ST), and the measured haematocrit        level, D_(H), and having its polynomial coefficients depending        on the analyte.

Once the analyte amount has been measured, the latter is usuallytranslated, for example directly by the measurement instrument, into aconcentration of analyte present in the sample, since the sample volumeis fixed and known. Since the concentration value is used, particularlyto implement an in vitro diagnosis, by comparing the measuredconcentration with predefined reference concentration values,characteristic of the diagnosis, the invention also aims at a method ofmeasuring an analyte concentration in a whole blood sample, whichcomprises:

-   -   measuring the haematocrit level of the whole blood sample;    -   measuring an analyte amount directly in the whole blood sample        and transforming it into a concentration based on the volume of        the tested sample; and    -   calculating a corrected analyte concentration according to        relation:        C _(P) =P _(a)(C _(ST) , D _(H))        where C_(p) is the corrected analyte concentration, C_(ST) is        the analyte concentration calculated from the measured amount        and from the sample volume, D_(H) is the measured haematocrit        level, and P_(a) is a non-constant polynomial of degree greater        than or equal to 1 having as indeterminate values the analyte        concentration obtained from the measured amount, C_(ST), and the        measured haematocrit level, D_(H), and having its polynomial        coefficients depending on the analyte.

In other words, the inventors have observed that it is possible tosubstantially correct the error on the amount/concentration directlymeasured on a whole blood sample by means of a non-constant polynomial,particularly of order greater than or equal to 1, having as unknowns,indeterminate values, or variables, the haematocrit level and theamount/concentration measured in the whole blood sample. The correctionaccording to the invention especially enables to obtain a relativemeasurement error with respect to a measurement conventionally directlyperformed on a plasma sample contained and often comprised within +/−10%over a wide range of amounts/concentrations. The correctedamount/concentration, having a value sufficiently close to that whichwould have been obtained by performing the measurement directly on aplasma sample, can thus be used, for example, to perform an in vitrodiagnosis so that it is no longer needed to carry out a priorcentrifugation step.

According to an embodiment, polynomial P_(a) comprises productD_(ST)×D_(H) of the measured analyte amount D_(ST) by the measuredhaematocrit level D_(H), or C_(ST)×D_(H) of the measured analyteconcentration C_(ST) by the measured haematocrit level D_(H).

More particularly, the corrected analyte amount is calculated accordingto relation:D _(P) =a ₀ +a ₁ ×D _(ST) +a ₂ ×D _(H) +a ₁₂ ×D _(ST) ×D _(H)where a₀, a₁, a₂ and a₁₂ are predetermined coefficients depending on theanalyte.

In other words, the polynomial involving the interaction between termsD_(ST) and D_(H), that is, first order terms D_(ST)×D_(H), isparticularly well adapted to ELISA, ELFA and immunocapture typeimmunoassay techniques.

Of course, coefficients a₀, a₁, a₂ and a₁₂ are also dependent on themeasurement system (analyte and haematocrit).

Similarly, the corrected analyte concentration is calculated accordingto relation:C _(P) =a′ ₀ +a ₁ ×C _(ST) +a′ ₂ ×D _(H) +a ₁₂ ×C _(ST) ×D _(H)where a′₀, a₁, a′₂ and a₁₂ are predetermined coefficients depending onthe analyte.

In other words, the polynomial involving the interaction between termsC_(ST) and D_(H), that is, first order terms C_(ST)×D_(H), isparticularly well adapted to ELISA, ELFA and immunocapture typeimmunoassay techniques.

Of course, coefficients a′₀, a₁, a′₂ and a₁₂ are also dependent on themeasurement system (analyte and haematocrit).

Particularly, where the analyte is a D-dimer in a concentrationmeasurement range from 45 ng/ml to 1,000 ng/ml, the coefficients areprovided by the following relations:

-   -   a′₀ is in the range from −29.311×0.9 to −29.311×1.1;    -   a₁ is in the range from 0.788×0.9 to 0.788×1.1;    -   a′₂ is in the range from 0.702×0.9 to 0.702×1.1; and    -   a₁₂ is in the range from 0.018×0.9 to 0.018×1.1.

More specifically:

-   -   a′₀=−29.311;    -   a₁=0.788;    -   a′₂=0.702; and    -   a₁₂=0.018.

Particularly, where the analyte is a troponin, for example, cardiactroponin I, in a concentration measurement range from 0.01 μg/l to 1.6μg/l, the coefficients are provided by the following relations:

-   -   a′₀ is in the range from −0.0052×0.9 to −0.0052×1.1;    -   a₁ is in the range from 0.9155×0.9 to 0.9155×1.1;    -   a′₂ is in the range from 0.0002×0.9 to 0.0002×1.1; and    -   a₁₂ is in the range from 0.0072×0.9 to 0.0072×1.1.

More specifically:

-   -   a′₀=−0.0052;    -   a₁=0.9155;    -   a′₂=0.0002; and    -   a₁₂=0.0072.

According to an embodiment, the measurement of the amount, and thus ofthe concentration of the analyte, is performed by an ELISA type or ELFAtype or immunocapture type technique. In other words, the measurementtechnique used is not modified with respect to measurement techniquesdirectly carried out on plasma. Immunoassay instruments of the state ofthe art can thus be used.

The invention also aims at a device for measuring the plasmatic amountof an analyte in a whole blood sample, characterized in that itcomprises

-   -   means for receiving said whole blood sample;    -   means for measuring the total analyte amount in the whole blood        sample;    -   means for calculating a corrected analyte amount according to        relation:        D _(P) =P _(a)(D _(ST) , D _(H))        where D_(p) is the corrected analyte amount, D_(ST) is the        measured analyte amount, D_(H) is the measured haematocrit        level, and P_(a) is a non-constant polynomial of a degree        greater than or equal to 1 having as indeterminate values the        measured analyte amount, D_(ST), and the measured haematocrit        level, D_(H), and having its polynomial coefficients depending        on the analyte.

The invention also aims at a device for measuring the plasmaticconcentration of an analyte in a whole blood sample, which comprises:

-   -   means for receiving said whole blood sample;    -   means for measuring the total analyte amount in the whole blood        sample;    -   means for transforming the analyte amount into a concentration;    -   means for inputting or for measuring the haematocrit level in        the whole blood sample; and    -   means for calculating a corrected analyte concentration        according to relation:        C _(P) =P _(a)(C _(ST) , D _(H))        where C_(p) is the corrected analyte concentration, C_(ST) is        the analyte concentration obtained from the measured amount,        D_(H) is the measured haematocrit level, and is a non-constant        polynomial of a degree greater than or equal to 1 having as        indeterminate values the measured analyte concentration C_(ST)        and the measured haematocrit level, and having its polynomial        coefficients depending on the analyte.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be better understood on reading of the followingdescription provided as an example only in relation with theaccompanying drawings, where:

FIGS. 1A to 1G are simplified views illustrating a state-of-the-art“sandwich” analyte concentration measurement of ELISA or ELFA type;

FIG. 2 is a flowchart illustrating a method according to the invention;

FIG. 3 is a plot illustrating the concentration and haematocrit levelhomogeneity of samples used to determine and verify a polynomialcorrection model applied to D-dimers;

FIG. 4 is a plot illustrating the D-dimer concentration measured inwhole blood, with no correction according to the invention, according tothe measured D-dimer concentration of the plasma;

FIG. 5 is a plot, for the samples of the verification set, of therelative correction error obtained according to the invention andaccording to a correction of the state of the art, according to theD-dimer concentration measured in plasma;

FIG. 6 is a plot, for the samples of the verification set, of theD-dimer concentration corrected according to the invention according tothe D-dimer concentration measured in plasma;

FIG. 7 is a plot of the D-dimer concentration corrected according to thestate of the art according to the D-dimer concentration measured inplasma;

FIG. 8 is plot, for the samples of the determination and verificationsets, illustrating the concentration and haematocrit level homogeneityof samples used to determine a polynomial correction model applied inthe context of the quantification of cardiac troponin I (TnI);

FIG. 9 is a plot illustrating the TnI concentration measured in wholeblood samples, with no correction according to the invention, accordingto the TnI concentration measured in plasma samples;

FIG. 10 is a plot, for the samples of the verification set, of therelative correction error obtained according to the invention andaccording to a correction of the state of the art, according to the TnIconcentration measured in plasma;

FIG. 11 is a plot of the TnI concentration corrected according to theinvention according to the TnI concentration measured in plasma; and

FIG. 12 is a plot of the corrected TnI concentration according to thestate of the art according to the TnI concentration measured in plasma.

DETAILED DESCRIPTION

Referring to the flowchart of FIG. 2, a method according to theinvention applied to a specific analyte will now be described.

The method comprises a step 10 of determining a mathematical modelcorrecting the measurement of the analyte amount/concentration on awhole blood sample, and a step 12 of using the mathematical modeldetermined at step 10 to deduce an unknown corrected analyteamount/concentration in a total blood sample sampled from a patient oran animal.

The determination of model 10 starts, at 14, with the forming of a setof pairs of whole blood and plasma samples originating from the samebatch, for example, from the same patient or animal, with a variablehaematocrit level and a variable analyte rate. The samples will be usedto determine and verify the mathematical model. Advantageously, thehaematocrit variation used for these samples is greater than the rangeobserved for the person or the animal having given the blood, andpreferably centered on the observed haematocrit average for the subjector a value close thereto. For example, the normal haematocrit values forman are from 40 to 54%, with an average at 45%, and from 37 to 47%, withan average at 42%, for woman, and the haematocrit level range used todetermine and verify the mathematical model is in the range from 26% to68%. The analyte concentration in the whole blood is selected to varybetween a low value characteristic of a healthy subject and a high valueprepared by overloading with a maximum 10% by volume of the whole bloodsample.

For example, a set of whole blood volumes is formed and each volume isdivided by two, the first sub-volume forming the whole blood sample andthe second sub-volume being centrifuged to obtain the plasma sample. Awhole blood volume may originate from a single subject, from a mixtureof a plurality of whole bloods sampled from different subjects, it maybe overloaded with analyte to set the analyte concentration, and/ororiginate from a first volume from which part of the plasma has beenremoved by centrifugation or to which plasma resulting from acentrifugation has been added to set the haematocrit level.

The method then carries on, at 16, for each pair of samples, by themeasurement of the analyte amount or concentration and of thehaematocrit level in the whole blood sample, and by measurement of theanalyte amount or concentration in the corresponding plasma sample. Theamounts are for example measured by means of technique of ELISA, ELFA,or immunocapture type of the state of the art. A set of triplets(D_(ST)(i), D_(P)(i), D_(H)(i)) is thus obtained, each comprising anamount D_(ST)(i) of analyte in the whole blood, an amount D_(P)(i) ofanalyte in the plasma, and a haematocrit level D_(H)(i) in the wholeblood. Of course, this can readily be applied to concentrationmeasurement by replacing analyte amounts with analyte concentrations.

Advantageously, triplets having aberrant values are then discarded,particularly those for which amount D_(ST)(i) measured in the wholeblood is greater than amount D_(P)(i) measured in the plasma. Hereagain, this is applicable to concentration measurement.

The obtained set of sample pairs is then divided into two subsets,containing an equal or different number, a first subset being used todetermine the mathematical model and a second subset being used toverify the determined mathematical model. The samples used to determinethe mathematical model are noted (D_(ST) ^(cal)(i), D_(p) ^(cal)(i),D_(H) ^(cal)(i)) and the samples used to verify the mathematical modelare noted (D_(ST) ^(verif)(i), D_(p) ^(verif)(i), D_(H) ^(verif)(i)).For example, two thirds of the pairs of samples are used to determinethe mathematical model and one third of the pairs is used for theverification thereof.

As known per se, the measurement technique used depends on the involvedanalyte, particularly due to the specific binding partners used to fixthe analyte, for example, by immobilization at the surface of a solidsurface, particularly a cone.

The measurement of the amount and of the concentration is implemented bymeans of one or a plurality of immunoanalyzers, such as for exampleBioMérieux's VIDAS® automaton. As known per se, an immunoanalyzercomprises one or a plurality of test sections capable of each receivingone or a plurality of test strips. Each strip comprises a plurality ofwells, one well receiving the sample to be analyzed and the other wellsrespectively containing the reagents used during the measurement,particularly diluent, a rinsing solution, a solution comprising theconjugate, and a solution containing the enzyme substrate. The automatonfurther comprises a mechanism for displacing the strip under a conehaving its surface containing a layer of binding partners specific tothe analyte. The cone is then positioned above each well and pipets in aspecific order the different mediums present therein while implementingintake, discharge, and incubation mechanisms specific to the measurementtechnique used. The automaton finally comprises a device for measuringthe property implied in this technique. For example, the VIDAS®automaton applies an ELFA-type technique which differs from thepreviously-described direct ELISA technique in that the substratecatalyzed by the enzyme function generates fluorescence, and itcomprises a fluorometer enabling to measure the fluorescence of thesolution contain in the last cuvette once the last washing step has beencarried out.

The haematocrit level is measured by means of any appropriate knowntechnique, for example, by means of the so-called microhaematocrittechnique used in the present embodiment, the Coulter technique, bylaser measurement, or by conductivity measurement.

At a next step 18 of the method, a calculation is implemented accordingto the determination triplets, for example (D_(ST) ^(cal)(i), D_(p)^(cal)(i), D_(H) ^(cal)(i)), to calculate the parameters of amathematical model for correcting an analyte amount directly measuredfrom a whole blood sample, more particularly a model according torelation:D _(P) =a ₀ +a ₁ ×D _(ST) +a ₂ ×D _(H) +a ₁₂ ×D _(ST) ×D _(H)   (2)where D_(p) is the corrected analyte amount, D_(ST) is the analyteamount directly measured on a whole blood sample, D_(H) is thehaematocrit level of the whole blood sample, and a₀, a₁, a₂, and a₁₂ arethe calculated coefficients of the mathematical model.

Advantageously, before applying the polynomial coefficients calculationalgorithm, variables D_(ST) and D_(H) of the polynomial according torelation (2) are normalized between −1 and 1. Particularly, if theanalyte amount in the whole blood has as a minimum value D_(ST) ^(min)and has as a maximum value D_(ST) ^(max), variable D_(ST) is transformedinto variable:

$X_{ST} = \frac{D_{ST} - c}{d}$${{where}\mspace{14mu} c} = {{\frac{D_{ST}^{\max} + D_{ST}^{\min}}{2}\mspace{14mu}{and}\mspace{20mu} d} = {\frac{D_{ST}^{\max} + D_{ST}^{\min}}{2}.}}$Similarly, if the haematocrit level has as a minimum value D_(H) ^(min)and has as a maximum value D_(H) ^(max), variable D_(H) is transformedinto variable

${X_{H} = \frac{D_{H} - e}{f}},\mspace{14mu}{{{with}{\mspace{11mu}\;}e} = {{\frac{D_{H}^{\max} + D_{H}^{\min}}{2}\mspace{14mu}{and}\mspace{14mu} f} = {\frac{D_{H}^{\max} + D_{H}^{\min}}{2}.}}}$

The model according to relation (2) can then be rewritten according torelation:D _(p) =a ₀ ^(n) +a ₁ ^(n) ×X _(ST) +a ₂ ^(n) ×X _(H) +a ₁₂ ^(n) ×X_(ST) ×X _(H)   (3)where coefficients a₀ ^(n), a₁ ^(n), a₂ ^(n) and a₁₂ ^(n) are determinedaccording to the least square method by minimizing a cost functionƒ(D_(P) ^(cal)(i)−(a₀ ^(n)+a₁ ^(n)×X_(ST) ^(cal)(i)+a₂ ^(n)×X_(H)^(cal)(i)+a₁₂ ^(n)×X_(ST) ^(cal)(i)×X_(H) ^(cal)(i)). Coefficients a₀,a₁, a₂ and a₁₂ can be easily deduced from coefficients a₀ ^(n), a₁ ^(n),a₂ ^(n) and a₁₂ ^(n)

The transformation of the variables is independent from the calculationalgorithm and enables to express each variable in the same scale andthus to compare the different coefficients a₁ ^(n), a₂ ^(n) and a₁₂^(n).

Here again, the foregoing is applicable to concentration measurement byreplacing the analyte amount with an analyte concentration. Thus, as avariation, the analyte amount measured in the whole blood sample istransformed into an analyte concentration by dividing the measuredamount by the volume of the whole blood sample, after which amathematical concentration correction model is calculated, particularlya model according to relation:C _(P) =a′ ₀ +a ₁ ×C _(ST) +a′ ₂ ×D _(H) +a ₁₂ ×C _(ST) ×D _(H)   (2bis)where C_(p) is the corrected analyte concentration, C_(ST) is theanalyte concentration calculated from the measured amount and from thesample volume, and where a′₀, a₁, a′₂ and a₁₂ are predeterminedcoefficients depending on the analyte, these coefficients being forexample calculated by a least square method. It should be noted that,since the analyte concentration is deduced from the amount, thecoefficients linked to the analyte concentration in the polynomial, thatis, coefficients a₁ and a₁₂, are the same for the two models expressedin amount and in concentration. However, the other coefficients, thatis, a′₀ and a′₂, are different.

Similarly, it is possible to apply a normalization of the variables ofthe polynomial of relation (2bis) similar to the normalization ofrelation (3), by calculating a mathematical model according to relation:C _(p) =a ₀ ^(n) ′+a ₁ ^(n) ′×Y _(ST) +a ₂ ^(n) ′×X _(H) +a ₁₂ ^(n) ′×Y_(ST) ×X _(H)   (3bis)where

${Y_{ST} = \frac{C_{ST} - s}{h}},{g = \frac{C_{ST}^{\max} + C_{ST}^{\min}}{2}},{h = \frac{C_{ST}^{\max} + C_{ST}^{\min}}{2}},$C_(ST) ^(min) is the minimum value of concentration C_(ST), C_(ST)^(max) is the maximum value of concentration C_(ST), and the polynomialcoefficients are coefficients which can easily be deduced from thepolynomial coefficients of relation (2bis).

The method then carries on, at 20, with the verification of thedetermined model by using the set of verification triplets, for example,(D_(ST) ^(verif)(i), D_(p) ^(verif)(i), D_(H) ^(verif)(i)) for theamount model.

More particularly, the determined model is advantageously verified basedon at least one of the following criteria:

-   -   relative error

$\frac{{D_{P}^{cor}(i)} - {D_{p}^{verif}(i)}}{D_{p}^{verif}(i)}$

-   -    between amount D_(p) ^(cor)(i) corrected by the mathematical        model, that is, D_(p) ^(cor)(i)=a₀+a₁×D_(ST)        ^(verif)(i)+a₂×D_(H) ^(verif)(i)+a₁₂×D_(ST) ^(verif)(i)×D_(H)        ^(verif)(i), and amount D_(p) ^(verif) measured in the plasma.        More particularly, it is verified whether the relative error is        centered on 0% and is in the range from −10% to +10%;    -   the parameters of a linear equation, for example, obtained        according to a so-called “Passing and Bablok” linear regression,        D_(p) ^(cor)(i)=α+β×D_(p) ^(verif)(i); and    -   biases calculated for different analyte amounts in the plasma by        using the above-described “Passing and Bablok” equation.

Here again, the foregoing can readily be applied to concentrationmeasurement by replacing the analyte amount with an analyteconcentration.

Once the determined model has been validated, the method carries on withthe exploitation, at 12, of this model for the analyteamount/concentration measurement directly performed on whole bloodsamples.

For example, the model is embarked in the data processing unit of animmunoanalyzer available for sale which may further be modified to beable to receive or calculate haematocrit level values. Otherwise, themodel is implemented on a processing unit independent from theimmunoanalyzer, for example, a personal computer. In this variation, anoperator inputs into the unit the analyte amount/concentration valuemeasured by the immunoanalyzer on a whole blood sample and the value ofthe haematocrit level measured for this sample and obtains in return thecorrected analyte amount/concentration.

Thus, for a whole blood sample of known volume for which the amount, andabove all the concentration, of analyte is desired to be known,exploitation step 12 starts, at 22, with the measurement of haematocritlevel D_(H) of the sample and carries on, at 24, with the measurement ofthe analyte amount/concentration directly in the whole blood sample bymeans of the same measurement technique, implemented by a sameimmunoanalyzer model as that used to determine and verify themathematical model.

A corrected analyte amount D_(p) is then calculated, at 26, according torelation (2) with coefficients a₀, a₁, a₂, and a₁₂ calculated ondetermination of model 10, or equivalently coefficients a₀ ^(n), a₁^(n), a₂ ^(n) and a₁₂ ^(n) of the model according to relation (3). Acorrected analyte concentration is calculated in the same way accordingto relation (2bis) or (3bis).

At 28, the concentration is calculated and then output, for example,displayed on a screen and/or recorded in a computer memory. Optionally,the corrected amount may also be output.

A method according to the invention where the measured amount orconcentration is corrected by a mathematical model has been described.

As previously described, measurement techniques are based on themeasurement of a property, for example, an optical, electrical,chemical, pH, or enzyme-linked property, having its value depending onthe analyte amount present in the analyzed sample. An immunoanalyzerthus comprises a device which measures such a property and outputs asignal corresponding to this measurement. According to the state of theart, the signal is then processed by means of a predeterminedmathematical model which transforms the signal into an amount and/orconcentration value.

As a variation, the method applies to the actual signal, before thetransformation thereof. Particularly, the signal measured on the wholeblood sample is corrected according to relation:S _(P) =a ₀ +a ₁ ×S _(ST) +a ₂ ×D _(H) +a ₁₂ ×S _(ST) ×D _(H)   (4)where S_(p) is the corrected signal and S_(ST) is the signal originatingfrom the measurement on the whole blood sample. The method applied tothe signal correction is similar to the previously-described method,provided to make minor modifications within the abilities of thoseskilled in the art. The calculation of a mathematical model withnormalized variables similar to relation (3) is also possible.

Two examples of application of the invention, respectively anapplication to the measurement of a D-dimer concentration and anapplication to the measurement of a cardiac troponin I concentrationwill now be described.

Measurement of the D-dimer Concentration

D-dimers are heterogeneous fibrin products all having epitope D-D formedby two continuous fibrin monomers covalently bonded by the enzymeresponsible for the blood coagulation crosslinking fibrin, or “XIIIa”factor. The assaying of D-dimers is mainly indicated in the diagnosis ofexclusion of venous thromboembolic diseases, particularly deep venousthrombosis and pulmonary embolism, the evaluation of the risk ofrecurrence of such diseases after the stopping of an anticoagulanttreatment, and in the diagnosis of disseminated intravascularcoagulation.

To determine and verify the mathematical model associated with theD-dimer, blood has been sampled from 186 healthy subjects on sodiumcitrate as an anticoagulant. More particularly, the blood has beencollected in tubes of 4.5 mL under vacuum containing 0.129 M oftrisodium citrate.

In order to have whole blood samples with a varied haematocrit level,the collected samples have been diluted with their own plasma after alight centrifugation, to obtain a haematocrit level varying in the rangefrom 26% to 61%. The haematocrit level is measured by means of themicrohaematocrit technique. The microhaematocrit is first acquired bycentrifugation of capillaries for 7 minutes at 10,000 rpm, after whichthe value of the haematocrit level is then deduced by means of a chart,as know per se in the state of the art.

In order to have whole blood and plasma samples with a varied D-dimerconcentration, the whole blood samples have been overloaded withD-dimer, before or after having varied the haematocrit level. Tooverload the samples, plasmas from bioMérieux's internal serum bank(Marcy L'Etoile, France) with a strong D-dimer concentration to beassayed have been used to have a distribution of the D-dimerconcentration in the whole blood in the 45 ng/mL-1,000 ng/mL range. Thewhole blood samples have been overloaded, particularly to 300 ng/mL, 500ng/mL, and 1,000 ng/mL, with an overload which does not exceed 10% ofthe volume of the whole blood sample to avoid modifying the originalblood matrix, that is, which does not exceed 1,000 ng/mL. The sampledistribution is uniform in the D-dimer concentration range obtained fromthe amount measured in the whole blood and in the haematocrit levelrange, as illustrated in FIG. 3, which shows the (concentrationsoriginating from the amounts measured in the whole blood, haematocritlevel) pairs for the model determination triplets (dots) and for themodel verification triplets (stars) The plasma samples are furtherobtained by centrifugation of a portion of each whole blood sample at3,000 rpm for 10 minutes.

As a numerical example, after the preparation of samples, the D-dimerconcentration in the whole blood is distributed in the range from 46.78ng/mL to 982.81 ng/mL, the haematocrit level is distributed in the rangefrom 26% to 61%, and the D-dimer concentration in the plasma isdistributed in the range from 96.86 ng/mL to 1,419.58 ng/mL.

The measurement of the D-dimer concentration in the whole blood andplasma samples comprises the enzyme immunoassay of fibrin degradationproducts (PDF) in human plasma by an ELFA-type technique, particularlyimplemented by a VIDAS® automaton with the “VIDAS D-dimère Exclusion II”kit designated with reference 30 455 of bioMérieux SA. Such ameasurement thus associates the sandwich-type enzyme immunoassay methodin two steps with a final fluorescence detection (ELFA). In a firststep, the sample is sampled, aspirated, and discharged a plurality oftimes so that the antigen can bind to the anti-FbDP antibodies (FbDP for“fibrinogen degradation products”) fixed on the cone. In a second step,a monoclonal anti-FbDP antibody marked with ALP (alkaline phosphatase)binds to the antigen already fixed on the cone to form a sandwich.Washing steps eliminate the non-fixed or excess compounds Thedevelopment step is then carried out. The 4MUP substrate(4-methyl-umbelliferyl-phosphate) is sucked in and then discharged intothe cone and the ALP catalyses the hydrolysis of the substrate intofluorescent 4MU (4-methyl-umbelliferone). The emitted fluorescence ismeasured at 450 nm. The value of the fluorescence signal is proportionalto the antigen amount in the sample.

FIG. 4 illustrates the D-dimer concentrations obtained fromconcentrations C_(ST)(i) measured in the whole blood samples accordingto the D-dimer concentrations obtained from amounts C_(p)(i) measured inthe respective plasma samples. A “Passing and Bablok”-type linearregression C_(ST)(i)=α+β×C_(p)(i) between the two amounts particularlyprovides α=−8.80 and β=0.69.

The triplets for which the concentrations measured in the whole bloodare greater than the concentrations in the plasma have been discarded.

One hundred and three triplets (C_(ST) ^(cal)(i), C_(p) ^(cal)(i), C_(H)^(cal)(i)) have been used to determine the mathematical model.

The following coefficients are thus obtained:

-   -   a′₀=806.279;    -   a₁ ^(n)=803.998 with a standard deviation equal to 11.917;    -   a′₂=196.295 with a standard deviation equal to 12.389; and    -   a₁₂ ^(n)=182.254 with a standard deviation equal to 25.909,

or, equivalently, with no normalization:

-   -   a′₀=−29.311;    -   a₁=0.788;    -   a′₂=0.702; and    -   a₁₂=0.018.

Fifty verification triplets (C_(ST) ^(verif)(i), C_(p) ^(verif)(i),C_(H) ^(verif)(i)) have further been used to verify the mathematicalmodel.

FIG. 5 illustrates relative error

$\frac{{C_{P}^{cor}(i)} - {C_{p}^{verif}(i)}}{C_{p}^{verif}(i)}$according to the D-dimer concentration obtained from the amount measuredin the plasma both for a correction C_(p) ^(cor)(i) according torelation (2bis) or (3bis) applied to the verification samples,represented by diamonds, and for a correction C_(p) ^(cor)(i) of thestate of the art performed according to relation (1) applied to theverification samples, represented by squares. As can be noted,conversely to the correction of the state of the art, the relative errorobtained by the invention is centered on zero, and is mainly in therange from −10% to 10%.

FIGS. 6 and 7 illustrate the corrected concentrations according to theconcentrations measured on plasma respectively according to thecorrection of relation (2bis) or (3bis) and according to the correctionof relation (1), and applied to the verification samples. The lineobtained by linear regression of “Passing and Bablok” type for each ofthe corrections is further calculated and plotted. The linecorresponding to the correction of the state of the art has a slopeequal to 1.18. The line corresponding to the invention is close toidentity with a slope equal to 1.03.

Finally, the biases for three D-dimer concentrations in the whole blood,that is, 250 ng/mL, 500 ng/mL, and 1,000 ng/mL, have been calculated andare respectively equal to −3.4%, −0.4%, and +1.1% for the correctionaccording to the invention, and are respectively equal to +6.7%, +12.5%,and +15.4% for the correction of the state of the art.

Concentrations corrected according to the invention similar to thoseobtained by a measurement directly performed on plasma can thus beobserved.

Similar results can be observed when the correction is performed on thesignal measured on the samples.

Measurement of the Cardiac Troponin I Concentration

Troponins (Tn) are proteins of the striated muscle. The striated muscleis formed of a thick filament, made of myosin, and of a thin filamentmade of actin, of tropomyosin, and or the troponin complex. This complexis itself formed of three sub-units, that is, the so-called “C”, “I”,and “T” troponins. Each of these troponins has skeletal and cardiacisoforms. Cardiac troponins are choice markers for the detection ofmyocardial necrosis and the assaying thereof enables to diagnose amyocardial infarction. The assaying of cardiac troponins is also usedfor the follow-up of a thrombolytic treatment and to estimate the sizeof the myocardial necrosis, as well as in the diagnosis of acutecoronary syndromes. The assaying of troponin “I”, noted TnI, alsoenables to highlight a heart impairment in the context of otherpathologies, particularly a renal failure, hypothyroidism, collagenoses,myopathies, or also pulmonary embolism.

To determine and verify the mathematical model associated with TnI,blood has been sampled from 186 healthy subjects on lithium heparinateas an anticoagulant. More particularly, the blood has been collected intubes of 4 mL containing 17 UI/mL of lithium heparinate.

The obtaining of whole blood samples with haematocrit levels and TnIconcentrations, and the obtaining of plasma samples from the whole bloodsamples are similar to those described in relation with the dosage ofD-dimers.

The measurement of the TnI concentration in the whole blood and plasmasamples comprises the enzyme immunoassay of troponin in human plasma byan ELFA-type technique, particularly implemented by a VIDAS® automatonwith the “VIDAS Troponine I Ultra” kit designated with reference 30 448of bioMérieux. In a single step, the sample is sampled and transferredinto the well containing the conjugates which are anti-TNI cardiacantibodies marked with ALP. The sample/conjugate mixture is sucked inand then discharged a plurality of times by the cone. This enables theTnI, on the one hand, to bind to the conjugate to form a sandwich.Washing steps eliminate the non-fixed or excess compounds. The ALPcatalyzes the hydrolysis of the substrate contained in the last well ofthe VIDAS® strip into fluorescent 4MU. The emitted fluorescence ismeasured at 450 nm. The value of the fluorescence signal is proportionalto the antigen concentration in the sample. At the end of the test, theresults are calculated from two calibration curves corresponding to thetwo development steps. A threshold signal manages the selection of thecalibration curve to be used for each sample.

The TnI concentration in the whole blood samples varies from 0.01 μg/Lto 1.4 μg/L and the haematocrit level varies from 22% to 73%, the TnIconcentration in the plasma thus varying from 0.01 μg/l to 1.6 μg/l.

The sample distribution is uniform in the TnI concentration rangemeasured in the whole blood and in the haematocrit level range, asillustrated in FIG. 8, which shows the (concentrations measured in thewhole blood, haematocrit level) pairs for the model determinationtriplets (dots) and for the model verification triplets (stars)

FIG. 9 illustrates the TnI concentration C_(ST)(i) obtained fromconcentrations measured in the whole blood samples according to the TnIconcentration C_(p)(i) measured in the respective plasma samples. A“Passing and Bablok”-type linear regression α=−0.01 between the twoconcentrations particularly provides α=−0.01 and β=0.84.

A total one hundred and eighty-seven samples have been prepared and anexchange algorithm, for example, a Fedorov algorithm, is implemented,for example, by software NEMRODW© of LPRAI Sarl. The Fedorov algorithmis an iterative algorithm which has the advantage of enabling to selectthe N best samples to determine the mathematical model, for example, the20 best samples among all the samples to calculate the parameters of themathematical model.

The following coefficients are obtained by means of the twenty selectedsamples:

-   -   a′₀=0.8982;    -   a₁ ^(n)=0.86751;    -   a′₂=0.1334; and    -   a₁₂ ^(n)=0.12413.

or equivalently:

-   -   a′₀=−0.0052;    -   a₁=0.9155;    -   a′₂=0.0002; and    -   a₁₂=0.0072.

One hundred and sixty-seven verification triplets (C_(ST) ^(verif)(i),C_(p) ^(verif)(i), C_(H) ^(verif)(i)) have further been used to verifythe mathematical model.

FIG. 10 illustrates relative error

$\frac{{C_{P}^{cor}(i)} - {C_{p}^{verif}(i)}}{C_{p}^{verif}(i)}$according to the TnI concentration obtained from the amount measured inthe plasma both for a correction C_(p) ^(cor)(i) according to relation(2bis) or (3bis) applied to the verification samples, represented bydiamonds, and for a correction C_(p) ^(cor)(i) of the state of the artperformed according to relation (1) applied to the verification samples,represented by squares. As can be noted, conversely to the correction ofthe state of the art, the relative error is centered on zero, and ismainly in the range from −10% to 10%. A few results outside of −/+10% inthe sample range where the TnI concentration is close to the detectionlimit can be observed.

FIGS. 11 and 12 illustrate the corrected TnI concentrations according tothe concentrations measured on plasma respectively according to thecorrection of relation (2bis) or (3bis) and the correction of relation(1), and applied to the verification samples. The line obtained bylinear regression of “Passing and Bablok” type for each of thecorrections is further calculated and plotted. The line corresponding tothe correction of the state of the art has a slope equal to 1.48. Theline corresponding to the invention is close to identity with a slopeequal to 1.02.

Finally, the biases for three TnI concentrations in the whole blood,that is, 0.1 μg/L, 0.5 μg/L, and 1 μg/L, have been calculated and arerespectively equal to 3.1%, 2.0%, and +1.9% for the correction accordingto the invention, and are respectively equal to +43.3%, +46.7%, and+47.1% for the correction of the state of the art.

The same results as those obtained for D-dimers can also be observed,that is, corrected concentrations which are similar to those obtained bya measurement directly performed on plasma.

Similar results can be observed when the correction is performed on thesignal measured on the samples.

Embodiments where a polynomial of first degree according to relation(2bis) or relation (3bis) is used have been described. A second degreepolynomial comprising the square of the haematocrit level and/or thesquare of the analyte amount/concentration measured in the whole bloodmay also be used. Similarly, a polynomial of higher degree may be used.

Particularly, the following procedure may be used to identify thepolynomial used:

-   a) setting the order of the polynomial to 1;-   b) calculating the parameters of the polynomial, for example, by    means of a least square method, as previously described;-   c) if the prediction error of the polynomial is considered    satisfactory, selecting this polynomial. For example, the prediction    error is calculated and if it is lower than a threshold,    advantageously 10%, the polynomial is selected; and-   d) if the prediction error, advantageously calculated on a set of    verification data, is not considered satisfactory, increasing the    order of the polynomial by one unit and repeating steps b), c),    and d) until the prediction error is considered satisfactory. As a    variation, these steps are repeated as long as the order is smaller    than or equal to 10, and preferably smaller than or equal to 5.

Of course, other methods of calculation and/or of final selection of thepolynomial may be used. For example, the order may also be calculated bymeans of a non-linear regression, as known per se in the state of theart. Similarly, a bayesian-type criterion, for example, the BIC(“bayesian information criterion”), may be used to select the finalpolynomial when a plurality of polynomials have been calculated.

Embodiments where the amount/concentration measurement is used with notransformation of the variables in the mathematical models have beendescribed. As a variation, a transformation of the measurement space maybe implemented, for example, a logarithmic transformation if themeasured amount/concentration range is significant. Term “measurement”thus means, in the sense of the invention, the direct or transformedmeasurement.

Similarly, polynomial coefficients calculated for a significantamount/concentration range have been described. As a variation, therange of amounts/concentrations may be divided into a plurality ofintervals and a mathematical model may be determined for each of theseintervals. The coefficients of the model may thus depend on theamount/concentration interval for which they are calculated.

The invention claimed is:
 1. A method of measuring an amount of analytein a whole blood sample, wherein the method comprises: performing acalibration of the method, wherein the calibration comprises: providinga plurality of calibration whole blood samples; measuring an haematocritlevel and an analyte amount directly in each of the plurality ofcalibration whole blood samples; measuring an analyte amount in a plasmasample from each of the plurality of calibration whole blood samples;and calculating polynomial coefficients of relation D_(P)=P_(a)(D_(ST),D_(H)) from values of haematocrit level and analyte amount measured inthe plurality of calibration whole blood samples, and values of analyteamount measured in the plasma samples from the plurality of calibrationwhole blood samples, where D_(P) is the measured analyte amount inplasma, D_(ST) is the measured analyte amount in whole blood, D_(H) isthe measured haematocrit level, and P_(a) is a non-constant polynomialof a degree greater than or equal to 1 having as indeterminate valuesthe measured analyte amount, D_(ST), and the measured haematocrit level,D_(H), said relation having polynomial coefficients depending on theanalyte; measuring an analyte amount directly in the whole blood sample;calculating a corrected analyte amount according to the relation:D _(P) =P _(a)(D _(ST) , D _(H)) where D_(P) is the corrected analyteamount, D_(ST)is the measured analyte amount, and D_(H) is the measuredhaematocrit level P_(a) D_(ST) D_(H); and providing the calculated valueof the corrected analyte amount.
 2. The method of claim 1, whereinpolynomial P_(a) comprises product D_(ST)×D_(H) of the measured analyteamount D_(ST) by the measured haematocrit level D_(H).
 3. The method ofclaim 1, wherein the corrected analyte amount is calculated according torelation:D _(P) =a ₀ +a ₁ ×D _(ST) +a ₂ ×D _(H) +a ₁₂ ×D _(ST) ×D _(H) where a₀,a₁, a₂ and a₁₂ are predetermined coefficients depending on the analyte.4. The method of claim 1, wherein the analyte amount/concentration ismeasured according to an immunoassay technique of ELISA type, of ELFAtype, or of immunocapture type.
 5. The method of claim 2, wherein thecorrected analyte amount is calculated according to relation:D _(P) =a ₀+a₁ ×D _(ST) +a ₂ ×D _(H) +a ₁₂ ×D _(ST) ×D _(H) where a₀,a₁, a₂ and a₁₂ are predetermined coefficients depending on the analyte.6. The method of claim 1, wherein the calibration includes performing averification comprising: providing a plurality of verification wholeblood samples; measuring an haematocrit level and an analyte amountdirectly in each of the plurality of verification whole blood samples;measuring an analyte amount in a plasma sample from each of theplurality of verification whole blood samples; calculating an analyteamount in the plasma sample from each of the plurality of verificationwhole blood samples according to the polynomial relationD_(P)=P_(a)(D_(ST), D_(H)) from the values of haematocrit level andanalyte amount measured in each of the plurality of verification wholeblood samples; and calculating a relative error between the calculatedvalues and the measured values of the analyte amounts in the plasmasamples from the plurality of verification whole blood samples.
 7. Themethod of claim 6, comprising comparing the relative error to at leastone threshold, wherein: if the relative error does not exceed the atleast one of the at least one threshold, the calibration is completed,and if the relative error exceeds at least one of the at least onethreshold, the verification comprises repeating the calculation of thecalibration with a non-constant polynomial P_(a) having one orderhigher.
 8. A method of measuring an analyte concentration in a wholeblood sample, wherein the method wherein the method comprises:performing a calibration of the method wherein the calibrationcomprises: providing a plurality of calibration whole blood samples;measuring an haematocrit level and an analyte amount directly in each ofthe plurality of calibration whole blood samples and transforming themeasured value of analyte amount in each of the plurality of calibrationwhole blood samples into a concentration; measuring an analyte amount ina plasma sample from each of the plurality of calibration whole bloodsamples and transforming the measured value of analyte amount in each ofthe plurality of plasma samples into a concentration; and calculatingpolynomial coefficients of relation C_(P)=P_(a)(C_(ST), D_(H)) fromvalues of haematocrit level and analyte concentration measured in theplurality of calibration whole blood samples, and values of analvteconcentration measured in the plasma samples from the plurality ofcalibration whole blood samples, where C_(P) is the measured analyteconcentration in plasma, C_(ST) is the measured analyte concentration inwhole blood, D_(H) is the measured haematocrit level, and P_(a) is anon-constant polynomial of a degree greater than or equal to 1 having asindeterminate values the measured analyte concentration, C_(ST), and themeasured haematocrit level D_(H), said relation having polynomialcoefficients depending on the analyte; measuring an analyte amountdirectly in the whole blood sample and transforming the measured amountinto a concentration by dividing the measured amount by the samplevolume; and calculating a corrected analyte concentration according tothe relation:C _(P) =P _(a)(C _(ST) , D _(H)) where C_(P) is the corrected analyteconcentration, C_(ST) is the measured analyte concentration, and D_(H)is the measured haematocrit level P_(a) C_(ST) D_(H); and providing thecalculated value of the corrected analyte concentration.
 9. The methodof claim 8, wherein the corrected analyte concentration is calculatedaccording to relation:C _(P) =a′ ₀ +a ₁ ×C _(ST) +a′ ₂ ×D _(H) +a ₁₂ ×C _(ST) ×D _(H) wherea′₀, a₁, a′₂ and a₁₂ are predetermined coefficients depending on theanalyte.
 10. The method of claim 9, wherein the analyte is a D-dimer,and wherein: a′₀ is in the range from −29.311×0.9 to −29.311×1.1; a₁ isin the range from 0.788×0.9 to 0.788×1.1; a′₂ is in the range from0.702×0.9 to 0.702×1.1; and a₁₂ is in the range from 0.018×0.9 to0.018×1.1.
 11. The method according to claim 9, wherein: a′₀=−29.311;a₁=0.788; a′₂=0.702; and a₁₂=0.018.
 12. The method of claim 9, whereinthe analyte is a cardiac troponin I, and wherein: a′₀ is in the rangefrom −0.0052×0.9 to −0.0052×1.1; a₁ is in the range from 0.9155×0.9 to0.9155×1.1; a′₂ is in the range from 0.0002×0.9 to 0.0002×1.1; and a₁₂is in the range from 0.0072×0.9 to 0.0072×1.1.
 13. The method accordingto claim 12, wherein: a′₀=−0.0052; a₁ =0.9155; a′₂=0.0002; anda₁₂=0.0072.
 14. The method of claim 8, wherein polynomial P_(a)comprises product C_(ST)×D_(H) of the measured analyte concentrationC_(ST) by the measured haematocrit level D_(H).
 15. The method of claim14, wherein the corrected analyte concentration is calculated accordingto relation:C _(P) =a′ ₀ +a ₁ ×C _(ST) +a′ ₂ ×D _(H) +a ₁₂ ×C _(ST) ×D _(H) wherea′₀, a₁,a′₂ and a₁₂ are predetermined coefficients depending on theanalyte.
 16. The method of claim 15, wherein the analyte is a D-dimer,and wherein: a′₀ is in the range from −29.311×0.9 to −29.311×1.1; a₁ isin the range from 0.788×0.9 to 0.788×1.1; a′₂ is in the range from0.702×0.9 to 0.702×1.1; and a₁₂ is in the range from 0.018×0.9 to0.018×1.1.
 17. The method according to claim 15, wherein: a′₀=−29.311;a₁=0.788; a′₂=0.702; and a₁₂=0.018.
 18. The method of claim 15, whereinthe analyte is a cardiac troponin I, and wherein: a′₀ is in the rangefrom −0.0052×0.9 to −0.0052×1.1; a₁ is in the range from 0.9155×0.9 to0.9155×1.1; a′₂ is in the range from 0.0002×0.9 to 0.0002×1.1; and a₁₂is in the range from 0.0072×0.9 to 0.0072×1.1.
 19. The method of claim8, wherein the calibration includes performing a verificationcomprising: providing a plurality of verification whole blood samples;measuring an haematocrit level and an analyte amount directly in each ofthe plurality of verification whole blood samples and transforming themeasured value of analyte amount in each of the plurality ofverification whole blood samples into a concentration; measuring ananalyte amount in a plasma sample from each of the plurality ofverification whole blood samples and transforming the measured value ofanalyte amount in each of the plurality of plasma samples from theplurality of verification whole blood samples into a concentration;calculating an analyte amount in the plasma sample from each of theplurality of verification whole blood samples according to thepolynomial relation C_(P)=P_(a)(C_(ST), D_(H)) from the values ofhaematocrit level and analyte concentration measured in each of theplurality of verification whole blood samples; and calculating arelative error between the calculated values and the measured values ofthe analyte concentration in the plasma samples from the plurality ofverification whole blood samples.
 20. The method of claim 19, comprisingcomparing the relative error to at least one threshold, wherein: if therelative error does not exceed the at least one of the at least onethreshold, the calibration is completed, and if the relative errorexceeds at least one of the at least one threshold, the verificationcomprises repeating the calculation of the calibration with anon-constant polynomial P_(a) having one order higher.
 21. A device formeasuring the plasmatic amount of an analyte in a whole blood sample,wherein the device comprises: means for performing a calibration of thedevice, wherein the calibration comprises: providing a plurality ofcalibration whole blood samples; measuring an haematocrit level and ananalyte amount directly in each of the plurality of calibration wholeblood samples; measuring an analyte amount in a plasma sample from eachof the plurality of calibration whole blood samples: and calculatingpolynomial coefficients of relation D_(P)=P_(a)(D_(ST), D_(H)) fromvalues of haematocrit level and analyte amount measured in the pluralityof calibration whole blood samples, and values of analyte amountmeasured in the plasma samples from the plurality of calibration wholeblood samples, where D_(P) is the measured analyte amount in plasma,D_(ST) is the measured analyte amount in whole blood, D_(H) is themeasured haematocrit level, and P_(a) is a non-constant polynomial of adegree greater than or equal to 1 having as indeterminate values themeasured analyte amount, D_(ST), and the measured haematocrit level,D_(H), said relation having polynomial coefficients depending on theanalvte; means for receiving said whole blood sample; means formeasuring the total analyte amount in the whole blood sample; means forcalculating a corrected analyte amount according to the relation:D _(P) =P _(a)(D _(ST) , D _(H)) where D_(P) is the corrected analyteamount, D_(ST) is the measured analyte amount, and D_(H) is the measuredhaematocrit level P_(a) D_(ST) D_(H) .
 22. The device of claim 21, whichis capable of implementing a method of measuring an amount of analyte ina whole blood sample, wherein the method comprises: measuring thehaematocrit level of the whole blood sample; measuring an analyte amountdirectly in the whole blood sample; and calculating a corrected analyteamount according to relation:D _(P) =P _(a)(D _(ST) , D _(H)) where D_(P) is the corrected analyteamount, D_(ST) is the measured analyte amount, D_(H) is the measuredhaematocrit level, and P_(a) is a non-constant polynomial of a degreegreater than or equal to 1 having as indeterminate values the measuredanalyte amount, D_(ST), and the measured haematocrit level, D_(H), andhaving its polynomial coefficients depending on the analyte, whereinpolynomial P_(a) comprises product D_(ST)×D_(H) of the measured analyteamount D_(ST) by the measured haematocrit level D_(H).
 23. A device formeasuring the plasmatic analyte concentration in a whole blood sample,wherein the device comprises: means for performing a calibration of thedevice, wherein the calibration comprises: providing a plurality ofcalibration whole blood samples; measuring an haematocrit level and ananalyte amount directly in each of the plurality of calibration wholeblood samples and transforming the measured value of analyte amount ineach of the plurality calibration whole blood samples into aconcentration; measuring an analyte amount in a plasma sample from eachof the plurality of calibration whole blood samples and transforming themeasured value of analyte amount in each of the plurality of plasmasamples into a concentration; and calculating polynomial coefficients ofrelation C _(P) =P _(a)(C _(ST) , D _(H)) from values of haematocritlevel and analyte concentration measured in the plurality of calibrationwhole blood samples, and values of analyte concentration measured in theplasma samples from the plurality of calibration whole blood samples,where C_(P) is the measured analyte concentration in plasma, C_(ST) isthe measured analyte concentration in whole blood, D_(H) is the measuredhaematocrit level, and P_(a) is a non-constant polynomial of a degreegreater than or equal to 1 having as indeterminate values the measuredanalyte concentration, C_(ST), and the measured haematocrit level,D_(H), said relation having polynomial coefficients depending on theanalyte; means for receiving said whole blood sample; means formeasuring the total analyte amount in the whole blood sample; means fortransforming the analyte amount into a concentration; means forinputting or for measuring the haematocrit level in the whole bloodsample; means for calculating a corrected analyte concentrationaccording to the relation:C _(P) =P _(a)(C _(ST) , D _(H)) where C_(P) is the corrected analyteconcentration, C_(ST) is the analyte concentration calculated from themeasured amount and from the sample volume, and D_(H) is the measuredhaematocrit level, P_(a) C_(ST) D_(H).
 24. The device of claim 23, whichis capable of implementing a method of measuring an analyteconcentration in a whole blood sample, wherein the method comprises:measuring the haematocrit level of the whole blood sample; measuring ananalyte amount directly in the whole blood sample and transforming themeasured amount into a concentration by dividing the measured amount bythe sample volume; and calculating a corrected analyte concentrationaccording to relation:C _(P) =P _(a)(C _(ST) , D _(H)) where C_(P) is the corrected analyteconcentration, C_(ST) is the measured analyte concentration, D_(H) isthe measured haematocrit level, and P_(a) is a non-constant polynomialof a degree greater than or equal to 1 having as indeterminate valuesthe measured analyte concentration, C_(ST), and the measured haematocritlevel, D_(H), and having its polynomial coefficients depending on theanalyte, wherein polynomial P_(a) comprises product C_(ST)×D_(H) of themeasured analyte concentration C_(ST) by the measured haematocrit levelD_(H).